Ultrasonic transducer for a metallic cavity implanted medical device

ABSTRACT

Implantable medical devices including an ultrasonic transducer and methods of optimizing an ultrasonic transducer of an implantable medical device are disclosed. The implantable medical device can include a housing, an ultrasonic transducer disposed within an interior of the housing, and a limiting structure configured to constrain deformation of the ultrasonic transducer. The limiting structure can include a separate structure coupled to the housing, or can comprise a resonant portion of the housing itself. During operation, the ultrasonic transducer is configured to communicate at a frequency at or near a resonant frequency of the housing.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. application Ser. No. 11/780,992, filed Jul. 20, 2007, now U.S. Pat. No. ______, which claims the benefit of Provisional Application No. 60/820,055, filed Jul. 21, 2006, both of which are herein incorporated by reference in their entirety for all purposes.

TECHNICAL FIELD

The present invention relates to transducers used in combination with an implantable medical device for wireless communication between the implantable medical device and remote devices implanted in the body. The present invention more particularly relates to ultrasonic transducers used in combination with a metallic cavity implantable medical device.

BACKGROUND

Implantable medical devices are often used to treat a variety of medical conditions. Examples of implantable medical devices include drug delivery devices, pain management devices, and devices that treat heart arrhythmias. One example of an implantable medical device used to treat heart arrhythmias is a cardiac pacemaker, which is commonly implanted in a patient to treat bradycardia (i.e., abnormally slow heart rate). A pacemaker includes a pulse generator and leads, which form the electrical connection between the pulse generator and the heart. An implantable cardioverter defibrillator (ICD) is used to treat tachycardia (i.e., abnormally rapid heart rate). An ICD also includes a pulse generator and leads that deliver electrical energy to the heart. Pulse generators typically include a metallic housing for a battery and electrical circuitry and a header for connecting the leads to the pulse generator.

Implantable medical devices are also useful in the treatment of heart failure. For example, cardiac resynchronization therapy (CRT) (also commonly referred to as biventricular pacing) is an emerging treatment for heart failure, which involves stimulation of both the right and left ventricles to increase hemodynamic efficiency and cardiac output. The treatment of heart failure and heart arrhythmias can be enhanced through the use of remote implanted devices. One example of such a remote device is a pressure sensor located in the vasculature. Communication between the implantable medical device and the remote device can allow the sensor data to be downloaded by a clinician used to modify the therapy delivered by the implantable medical device, or both. There is therefore a need for an implantable medical device that includes a transducer for communication with a remote implanted device.

SUMMARY

The present invention, according to one embodiment is an implantable medical device comprising a housing and an ultrasonic transducer having a communication frequency coupled to a portion of the housing. The housing resonates at the communication frequency, and a casing is coupled to the housing and disposed over the ultrasonic transducer. The casing is adapted to amplify the deformation of the ultrasonic transducer in a bending mode and transfer the bending moment to the housing.

The present invention, according to another embodiment, is an implantable medical device comprising a housing having an upper portion and a lower portion. A first ultrasonic transducer is coupled to a first connection rod and is coaxial with the first connection rod. The first ultrasonic transducer and first connection rod are interposed between the upper and lower portions such that the first ultrasonic transducer is adapted to vibrate the upper and lower portions simultaneously.

The present invention, according to yet another embodiment, is a method of optimizing an ultrasonic transducer and a housing of an implantable medical device. The method comprises determining system level requirements for the ultrasonic transducer and selecting an initial ultrasonic transducer based on the system level requirements. A first finite element methods analysis is conducted to verify the feasibility of the initial ultrasonic transducer, and a second finite element methods analysis and water tank experiments are conducted to determine whether the housing and ultrasonic transducer have a desired vibration mode at a targeted ultrasonic communication frequency. The ultrasonic transducer or the design of the housing are optimized based on the results of the first and second finite element methods analysis and water tank experiments. The resonance frequency and amplitude of the optimized ultrasonic transducer are verified using finite element method analysis and water tank experiment. A final ultrasonic transducer and housing design are selected based upon the results of the verifying step.

While multiple embodiments are disclosed, still other embodiments of the present invention will become apparent to those skilled in the art from the following detailed description, which shows and describes illustrative embodiments of the invention. Accordingly, the drawings and detailed description are to be regarded as illustrative in nature and not restrictive.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a combined cutaway and perspective view of an implantable medical device in accordance with one embodiment of the present invention.

FIG. 2 is a front view of the inside of the implantable medical device of FIG. 1 in accordance with one embodiment of the present invention.

FIGS. 3A-3B depict various views of the implantable medical device of FIG. 2.

FIGS. 4A-4B are various views of an implantable medical device in accordance with another embodiment of the present invention.

FIGS. 5A-5B are various views of an implantable medical device in accordance with yet another embodiment of the present invention.

FIG. 6 is a cross-sectional view of an implantable medical device in accordance with another embodiment of the present invention.

FIGS. 7A-7B are various views of an implantable medical device in accordance with another embodiment of the present invention.

FIG. 8 is a cross-sectional view of an implantable medical device in accordance with yet another embodiment of the present invention.

FIGS. 9A-9B are various views of an implantable medical device in accordance with another embodiment of the present invention.

FIGS. 10A-10B are various views of an implantable medical device in accordance with another embodiment of the present invention.

FIGS. 11A-11B are various views of an implantable medical device in accordance with another embodiment of the present invention.

FIG. 12 is a cross-sectional view of an implantable medical device in accordance with yet another embodiment of the present invention.

FIG. 13 is a cross-sectional view of an implantable medical device in accordance with yet another embodiment of the present invention.

FIG. 14 is a flowchart depicting an exemplary method of optimizing an implantable medical device having an acoustic transducer in accordance with the present invention.

While the invention is amenable to various modifications and alternative forms, specific embodiments have been shown by way of example in the drawings and are described in detail below. The intention, however, is not to limit the invention to the particular embodiments described. On the contrary, the invention is intended to cover all modifications, equivalents, and alternatives falling within the scope of the invention as defined by the appended claims.

DETAILED DESCRIPTION

FIG. 1 is a perspective view of an implantable medical device (IMD) 10. The IMD 10 includes a pulse generator 12 and a cardiac lead 14. The lead 14 operates to convey electrical signals between the heart 16 and the pulse generator 12. A proximal end 18 of the lead 14 is coupled to the pulse generator 12 and a distal end 20 is coupled to the heart 16. The lead 14 includes a lead body 17 extending from the lead proximal end 18 to the lead distal end 20.

The heart 16 includes a right atrium 22, a right ventricle 24, and a pulmonary artery 26. A tricuspid valve 28 is located between and controls the flow of blood from the right atrium 22 and the right ventricle 24. A pulmonic valve 30 is located between and controls the flow of blood from the right ventricle 24 to the pulmonary artery 26. The heart 16 also includes a left atrium 32, a left ventricle 34, and an aorta 36. A mitral valve 38 is located between and controls the flow of blood from the left atrium 32 to the left ventricle 34. An aortic valve 40 is located between and controls the flow of blood from the left ventricle 34 to the aorta 36. In one embodiment, the IMD 10 includes a plurality of leads 14. For example, it may include a first lead 14 adapted to convey electrical signals between the pulse generator 12 and the left ventricle 34 and a second lead 14 adapted to convey electrical signals between the pulse generator 12 and the right ventricle 24.

In the embodiment shown in FIG. 1, a helical electrode 42 penetrates the endocardium 43 of the right ventricle 24 and is embedded in the myocardium 44 of the heart 16. When positioned as above, the electrode 42 can be used to sense the electrical activity of the heart 16 or to apply a stimulating pulse to the right ventricle 24. In other embodiments, the cardiac lead 14 of the present invention can also be implanted in any other portion of the heart 16 as known in the art. For example, it may be implanted in the right atrium 22, the right ventricle 24, the pulmonary artery 26, the left ventricle 34, or in the coronary veins. In one embodiment, the IMD 10 includes multiple electrodes 42 disposed to sense electrical activity and/or deliver therapy to both the left and right sides of the heart 16. In one embodiment, the lead 14 can be an epicardial lead where the electrode 42 penetrates the epicardium 45.

As shown in FIG. 1, a remote device 46 is located in the pulmonary artery 26. Alternatively, the remote device 46 could be located in the right ventricle 24, the aorta 36, or any other location in or near the heart 16 or vasculature. The remote device 46 shown in FIG. 1 comprises a pressure sensor. The remote device 46 shown in FIG. 1 can be used to measure pressure in the pulmonary artery 26. In one embodiment, the remote device 46 measures end-diastolic pressure in the pulmonary artery 26. The sensed pressure can be used to predict decompensation of a heart failure patient or to optimize pacing or defibrillation therapy. One example of a pressure sensor 46 adapted to measure pressure is disclosed in U.S. Pat. No. 6,764,446 to Wolinsky et al.

While the IMD 10 shown in FIG. 1 comprises a cardiac pacemaker, in other embodiments, the IMD 10 could comprise any other medical device suitable for implantation in the body. For example, the IMD 10 could comprise a drug delivery device or a pain management device. The remote device 46 can comprise any type of chronically implanted device or remote sensor adapted to deliver therapy or monitor biological functions. The remote device 46 can be located anywhere in the body adapted for sensing a desired biological parameter or delivering therapy. For example, the remote device 46 could comprise a volume sensor or sense any other cardiac parameter, such as maximum or minimum pressure, or calculate a cardiac parameter derivative, such as the slope of the pressure. In other embodiments, the remote device 46 could comprise a glucose level monitor, a pulmonary sound sensor, a satellite pacing device, or any other remote sensing or therapy-delivering device. A plurality of remote devices 46 could be implanted throughout the body and in wireless communication with each other and with an IMD 10.

FIG. 2 depicts a front view of the inside of the pulse generator 12. The pulse generator 12 includes a housing 48 and a header 50. An acoustic transducer 52 is attached to the inside of the housing 48 and is electrically connected to control circuitry (not shown). The acoustic transducer 52 can be used as a sensor, an actuator, or as both a sensor and an actuator. FIGS. 3A-3B depict cross-sectional views of the housing 48. The acoustic transducer 52 includes electrodes 54 and can be coupled to the inside of the housing 48 by an insulating bonding layer 55. In the embodiment shown in FIG. 2, the acoustic transducer 52 has a circular shape, but the acoustic transducer could take any other shape, such as rectangular, beam-shaped, circular, annular, or triangular.

In one embodiment, the acoustic transducer 52 comprises a piezoelectric material. Piezoelectric materials adapted for use in the acoustic transducer 52 include piezo polymer, piezo crystal, or piezo ceramic materials. In one embodiment, the acoustic transducer 52 can comprise a polyvinylidine difluoride (PVDF) material. In another embodiment, the acoustic transducer 52 can comprise a lead zirconate titanate (PZT) material. In yet another embodiment, the acoustic transducer can comprise a piezo single crystal material, such as lead magnesium niobate-lead titanate (PMN-PT). In other embodiments, the acoustic transducer 52 can comprise a cMUT transducer. In one embodiment where a PZT material is used, the thickness of the PZT material is approximately equivalent to the thickness of the housing 48. In one embodiment, the acoustic transducer 52 comprises PZT5A material, has a diameter of 25.4 millimeters or less, and has a thickness of 3 millimeters or less.

As shown in FIGS. 3A-3B, one electrode 54 is connected to an AC voltage source and the other electrode 54 is connected to ground. (The thickness of the electrodes 54 in the Figures is not shown to scale.) The AC voltage can be applied to the acoustic transducer 52 to cause it to vibrate at a desired frequency. Alternatively, both electrodes 54 could be driven simultaneously by an H-bridge, as is known to one of skill in the art. In one embodiment, the acoustic transducer 52 has a mechanical resonance of greater than approximately 20 kiloHertz. In another embodiment, the acoustic transducer 52 has a mechanical resonance at a frequency of approximately 40 kiloHertz. In yet another embodiment, the acoustic transducer 52 can operate in an electrically resonant mode.

In one embodiment, the acoustic transducer 52 is adapted to generate and receive acoustic waves having a frequency greater than approximately 20 kiloHertz, has a transmit sensitivity greater than approximately 100 Pascals per Volt at 0.25 meters of water or transmitting voltage response (TVR) greater than approximately 148 decibels (dB) referenced to (re) 1 microPascal per Volt at 1 meter of water, has a receive sensitivity greater than approximately 0.5 milliVolt per Pascal or free-field voltage sensitivity (FFVS) greater than −186 dB re 1 Volt per microPascal, and has a total static capacitance less than or equal to approximately 20 nanoFarads. In another embodiment, the acoustic transducer 52 is adapted to generate and receive acoustic waves having a frequency of approximately 40 kiloHertz, has a transmit sensitivity greater than approximately 200 Pascals per Volt at 0.25 meters of water or TVR greater than approximately 154 decibels re 1 microPascal per Volt at 1 meter of water, has a receive sensitivity greater than approximately 0.5 milliVolts per Pascal or FFVS greater than −186 dB re 1 Volt per microPascal, and a total static capacitance less than or equal to approximately 8 nanoFarads.

The acoustic transducer 52 can be used for wireless communication between the IMD 10 and the remote device 46. As shown in FIG. 3B, acoustic signals are transmitted from the IMD 10 to the remote device 46 by applying an AC voltage or a charge change to the acoustic transducer 52 so that the acoustic transducer 52 deforms and the pulse generator housing 48 vibrates in response to the deformation. Acoustic signals sent from the remote device 46 are received by the acoustic transducer 52 when an impinging acoustic wave results in mechanical vibration of the housing 48, thus causing a voltage change or a charge density change in the acoustic transducer 52, which is detected by control circuitry (not shown).

FIGS. 4A-4B depict an embodiment of the present invention where a casing 62 encloses the acoustic transducer 52. The casing 62 serves two functions. First, it bends when the acoustic transducer 52 deforms, thereby applying a bending moment to the housing 48. Second, it mechanically amplifies the deformation of the acoustic transducer 52, particularly when the housing 48 has a resonant mode at the desired frequency. In one embodiment, the casing 62 has a diameter of greater than 25 millimeters, a height of less than 4 millimeters, a top thickness of between 0.2 and 1 millimeter, and a wall thickness of between 3 to 6 millimeters. In one embodiment, the acoustic transducer 52 is attached to the casing 62 and there may be a gap or space between the acoustic transducer 52 and the housing 48. In another embodiment, the acoustic transducer 52 is attached to the housing 48 and there may be a gap between the acoustic transducer 52 and the casing 62.

FIGS. 5A-5B and 6 depict alternative embodiments of an IMD 10 having an acoustic transducer 52. As shown in FIGS. 5A-5B, the housing 48 includes annular regions 64 having a thinner cross-section than a substantial portion of the housing 48. The regions 64 shown in FIG. 5A comprise a “bull's eye” but alternatively could have any other shape, including a plurality of rectangles or circles. As shown in FIG. 5B, the acoustic transducer 52 is adjacent to the regions 64, thereby allowing for increased vibration, movement, and/or deformation of the housing 48. In one embodiment, the thickness of the regions 64 is approximately 0.12 millimeter. FIG. 6 depicts an alternative housing 48 where the region 64 takes the form of a corrugated or wavy region of the housing 48 located underneath the acoustic transducer 52. The gaps 66 shown in FIGS. 5A-5B and 6 can contain air, nitrogen, some other gas, or vacuum. As shown, FIGS. 5A-5B and 6 include the casing 62 described with respect to FIGS. 4A-4B, but in alternative embodiments, the casing 62 need not be present.

FIGS. 7A-7B depict an alternative embodiment of an IMD 10 having an acoustic transducer 52. In this embodiment, the acoustic transducer 52 has an annular shape. The acoustic transducer 52 acts as a limiting structure and defines the resonance characteristics of the region 56 by establishing boundary conditions for the region 56. The resonance characteristics of the region 56 enhance the performance of the acoustic transducer 52. When acoustic waves having the same frequency as the resonant frequency of the region 56 impact the region 56, the region 56 vibrates, resulting in deformation of the acoustic transducer 52. This deformation results in a voltage or a charge change in the acoustic transducer 52, which is detected by the control circuitry. Driving the acoustic transducer 52 using an AC voltage or an H-bridge at the resonant frequency results in periodic deformation of the acoustic transducer 52. This deformation causes the region 56 to vibrate at the resonant frequency, thereby transmitting an acoustic wave from the region 56 at the desired frequency.

The dimensions of the acoustic transducer 52 can be determined using the following formula from Blevins, “Formulas for Natural Frequencies and Mode Shapes”, ISBN 1-57524-184-6, herein incorporated by reference in its entirety:

$f = {\frac{\lambda^{2}}{2 \cdot \pi \cdot a^{2}}\sqrt{\frac{E \cdot h^{2}}{12 \cdot \gamma \cdot \left( {1 - v^{2}} \right)}}}$

As used in the above equation, a is the plate radius, h is the plate thickness, E is Young's modulus, ν is Poisson's ratio, ρ is the density, γ is the mass per unit area or ρ*h, and λ is a dimensionless frequency parameter dependent on the mode shape that can be found in Blevins.

In one embodiment, the acoustic transducer 52 comprises a PZT material and defines a region 56 having a mechanical resonance of greater than approximately 20 kiloHertz. In one embodiment where the housing 48 comprises titanium and λ=3.19 for mode 00, E=116 GigaPascals, ν=0.3, h=0.3 millimeters, and ρ=4500 kg/m³, and a=4.2 millimeters, for an annular piezoelectric transducer 52 with an inner radius of 4.2 millimeters, an outer radius of 8.4 millimeters, and a thickness of 2 millimeters, the natural frequency f of the first mode of the region 56 is at 40 kHz. The acoustic transducer 52 can be bonded to the housing 48 using epoxy or medical adhesive. Blevins provides additional mode resonant frequency formulas for additional shapes and boundary conditions.

In the embodiment shown in FIG. 8, the acoustic transducer 52 is mechanically bonded to a non-active limiting structure 58. As shown, the limiting structure 58 has an annular shape and defines the resonant region 56. Use of the non-active limiting structure 58 improves both the transmit and receive sensitivity of the acoustic transducer 52 when the resonant region 56 which has the same resonant frequency as the acoustic transducer 52. The non-active limiting structure 58 transfers deformation between the acoustic transducer 52 and the housing 48. For example, when the acoustic transducer 52 is in a receive mode, an impinging acoustic wave causes the resonant region 56 to vibrate, and the resulting deformation is transferred to the acoustic transducer 52 through the non-active limiting structure 58. When the acoustic transducer 52 is in a transmit mode, actuation of the acoustic transducer 52 causes it to vibrate at the resonant frequency, which is then transferred to the housing 48 by the non-active limiting structure 58, thus causing the resonant region 56 to vibrate at the resonant frequency. The non-active limiting structure 58 can be comprised of titanium, aluminum, stainless steel, ceramic material, or any other rigid material. The gap 60 between the acoustic transducer 52 and the resonant region 56 can be filled with air, nitrogen, some other gas, or vacuum.

FIGS. 9A-9B depict an alternative embodiment of the IMD 10. As shown in FIG. 9A, the limiting structure 58 is located in a corner 70 of the housing 48, has an approximately semicircular shape, and defines a resonant region 56. The acoustic transducer 52 is bonded to the housing 48 and extends from the limiting structure 58 into the resonant region 56. In one embodiment, the length of the acoustic transducer 52 is determined by the strain/stress profile of the resonant region 56. In one embodiment, the deformation of the acoustic transducer 52 is constrained by the limiting structure 58 and the acoustic transducer 52 has a length of no more than half of the radius of the resonant region 56. As shown in the cross-sectional view of FIG. 9B, the limiting structure 58 does not extend to the rear wall 72 of the housing, but in an alternative embodiment, the limiting structure 58 could extend to the rear wall 72. In yet another alternative embodiment, the limiting structure 58 could be located on the outside of the housing 48. In one embodiment, the limiting structure 58 could take the shape of an annular ring located on the outside of the housing 48.

FIGS. 10A-10B depict yet another alternative embodiment of the present invention. In this embodiment, the acoustic transducer 52 is located in the corner 70 of the housing 48. The checkerboard pattern shown in FIG. 10A represents the mode shape of the housing 48 at approximately 40 kiloHertz. The regions 73 represent regions of the housing 48 that are moving in the Z-axis. These regions 73 can be moving either in a positive or negative direction along the Z-axis. The dotted regions 73 can be moving in a positive direction along the Z-axis while the undotted regions can be moving in a negative direction along the Z-axis. The lines 74 of the checkerboard pattern represent the nodal regions, or lines where the housing is motionless with respect to the Z-axis. In the embodiment shown, the corner 70 acts as a limiting structure and defines a resonant region 56, but in other embodiments, the transducer 52 could be located in a region 73 where the nodal lines 74 create a resonant region 56. As shown, the acoustic transducer 52 is bonded to the top face 76 and is located in the resonant region 56. In one embodiment, the acoustic transducer 52 is located in a region of maximum stress and strain. In other embodiments, the shape of the housing 48 itself can be changed to obtain a desired frequency characteristic. In other embodiments, the housing 48 could be embossed or include a “dimple” to obtain a desired frequency characteristic.

FIGS. 11A-11B show another alternative embodiment of the IMD 10 of the present invention. In this embodiment, the header 50 acts as a limiting structure on the acoustic transducer 52. An aperture 78 is located in the header 50 and defines a resonant region 56. The acoustic transducer 52 extends into the resonant region 56 and is bonded to the inside of the housing 48.

FIG. 12 shows a cross-sectional view of an alternative embodiment of the IMD 10 of the present invention. The IMD 10 includes a housing 48 having an upper portion 48 a and lower portion 48 b. A connection rod 84 is coupled to the upper portion 48 a and a second connection rod 84 is coupled to the lower portion 48 b. An acoustic transducer 52 is interposed between the two connection rods 84. The connection rods 84 have a bell shape in FIG. 12, but could have any other shape. When the acoustic transducer 52 of FIG. 12 is actuated, the portions 48 a, 48 b will vibrate, propagating acoustic waves in two directions. The thickness of the acoustic transducer 52 can be adjusted according to the desirable actuation displacement of the housing 48 for generation of acoustic waves.

FIG. 13 shows a cross-sectional view of an alternative embodiment where an acoustic transducer 52 is coupled to each portion 48 a, 48 b and two connection rods 84 are interposed between the acoustic transducers 52. The structure depicted in FIG. 13 also allows acoustic waves to propagate in two directions simultaneously. The symmetrical design of FIG. 13 allows for easier design and manufacture of the acoustic transducers 52 and connection rods 84.

The embodiments shown in FIGS. 12 and 13 increase the sensitivity of the acoustic transducer or transducers 52. The acoustic transducer or transducers 52 can comprise a piezoelectric material such as PZT or PVDF. In FIGS. 12 and 13, the portions 48 a, 48 b can apply a pre-stress to the acoustic transducer or transducers 52. In one embodiment, the acoustic transducer or transducers 52 and connection rods 84 are resonant in the thickness mode. In another embodiment, the acoustic transducer or transducers 52 and connection rods 84 are resonant in a radial mode. In one embodiment, the combined thickness of the connection rod 84 and the acoustic transducer 52 is approximately half of the wavelength of the communication frequency. In one embodiment, the combined thickness of the connection rod 84 and the acoustic transducer 52 is between 6 and 7 millimeters. In an alternative embodiment, a single connection rod 84 and a single acoustic transducer 52 are interposed between the portions 48 a, 48 b. In one embodiment, the single acoustic transducer 52 comprises a PZT material 1 centimeter in diameter and 1 millimeter thick. The connection rod 84 has a height of about 6 millimeters, a minimum diameter of 1 centimeter, a maximum diameter of 2.5 centimeters, and a taper beginning at a height of approximately 3 millimeters. In one embodiment, the thickness of the housing 48 is between 0.3 to 2 millimeters and the width of the housing 48 is between about 2.5 to 5 centimeters.

FIG. 14 depicts an exemplary method 200 for optimizing an acoustic transducer 52 and an IMD 10 for wireless communication with a remote device 46. System level requirements such as the power budget, transducer sensitivity, mechanical size, material selection, and the vibration mode of the metallic housing 48 are determined (block 210). An initial acoustic transducer 52 is selected based on the system level requirements (block 220). A Finite Element Methods (FEM) analysis, as is known to those of skill in the art, is performed to verify the feasibility of the initial transducer in simplified geometries (block 230). In this embodiment, verifying the feasibility includes determining whether the acoustic transducer 52 system level attributes fall within an acceptable range for the system level requirements. FEM and water tank experiments are used to determine whether the metallic housing 48 and acoustic transducer 52 have the desired vibration mode at the targeted ultrasonic communication frequency (block 240). The design can be optimized by varying the design of the housing 48, incorporating a casing 62, modifying the design 62 of the casing, modifying the characteristics of the acoustic transducer 52, including the dimensions, or any combination thereof (block 250).

Once the design is further refined, the underwater resonance frequency and amplitude of the acoustic transducer 52 can be verified through Finite Element Method models and water tank experiments (block 260). The experiments can be conducted in a water tank using a hydrophone and can utilize a scanning laser vibrometer (SLV). One such SLV can be obtained from Polytec GmbH, Polytec-Platz 1-7, D-76337 Waldbronn, Germany. The design can again be optimized by varying the parameters such as housing 48 design, acoustic transducer 52 design, etc. (block 250). This optimization is repeated until the desired resonance characteristics are obtained and a final acoustic transducer design is reached (block 270).

The invention has been described with respect to implantable medical devices such as pacemakers and defibrillators, but could be adapted for use in any other implantable medical device, such as an insulin pump, neurostimulator, drug delivery system, pain management system, heart or lung sound sensor, or any other implantable medical device. The remote device 46 can comprise any type of chronically implanted device or remote sensor adapted to deliver therapy or monitor biological functions, such as pressure sensor, glucose level monitor, a pulmonary sound sensor, volume sensor, satellite pacing device, or any other remote sensing or therapy-delivering device, and can be located anywhere in the body adapted for sensing a desired biological parameter or delivering therapy. A plurality of remote devices 46 could be implanted throughout the body and in wireless communication with each other and with an IMD 10.

Various modifications and additions can be made to the exemplary embodiments discussed without departing from the scope of the present invention. For example, while the embodiments described above refer to particular features, the scope of this invention also includes embodiments having different combinations of features and embodiments that do not include all of the described features. Accordingly, the scope of the present invention is intended to embrace all such alternatives, modifications, and variations as fall within the scope of the claims, together with all equivalents thereof. 

1. An implantable medical device, comprising: a housing; an ultrasonic transducer disposed within an interior of the housing, the ultrasonic transducer configured to communicate at a frequency at or near a resonance frequency of the housing; and a limiting structure configured to constrain deformation of the ultrasonic transducer.
 2. The implantable medical device of claim 1, wherein the limiting structure comprises an annular-shaped structure.
 3. The implantable medical device of claim 1, wherein the limiting structure comprises a corner of the housing.
 4. The implantable medical device of claim 1, wherein the limiting structure comprises a header coupled to the housing.
 5. The implantable medical device of claim 4, further comprising an aperture located in the header, and wherein the ultrasonic transducer extends into a resonant region defined by the aperture.
 6. The implantable medical device of claim 1, wherein the ultrasonic transducer is secured to the housing and extends from the limiting structure to a resonant region of the housing.
 7. The implantable medical device of claim 1, wherein the limiting structure extends to a rear wall of the housing.
 8. The implantable medical device of claim 1, wherein the limiting structure is located inside the housing.
 9. The implantable medical device of claim 1, wherein the limiting structure is located outside of the housing.
 10. The implantable medical device of claim 1, wherein the limiting structure is a non-active limiting structure.
 11. The implantable medical device of claim 1, further comprising a casing coupled to the housing and disposed over the ultrasonic transducer, wherein the casing is adapted to amplify the deformation of the ultrasonic transducer in a bending mode and transfer the bending moment to the housing.
 12. An implantable medical device, comprising: a housing; and an ultrasonic transducer disposed over an undulating portion of the housing, the ultrasonic transducer configured to communicate at a frequency at or near a resonance frequency of the housing.
 13. The implantable medical device of claim 12, wherein the undulating portion comprises a thinned region of the housing having a thinner cross-section than a substantial portion of the housing.
 14. The implantable medical device of claim 13, wherein the thinned region is annular shaped.
 15. The implantable medical device of claim 12, wherein the undulating portion comprises a wavy or corrugated portion of the housing.
 16. The implantable medical device of claim 12, further comprising a gas-filled gap or vacuum disposed between the ultrasonic transducer and the undulating portion of the housing.
 17. The implantable medical device of claim 12, further comprising a casing coupled to the housing and disposed over the ultrasonic transducer, wherein the casing is adapted to amplify the deformation of the ultrasonic transducer in a bending mode and transfer the bending moment to the housing.
 18. A method of optimizing an ultrasonic transducer and a housing of an implantable medical device, the method comprising: determining system level requirements for the ultrasonic transducer; selecting an initial ultrasonic transducer based on the system level requirements; conducting a first finite element methods analysis to verify the feasibility of the initial ultrasonic transducer; conducting a second finite element methods analysis and water tank experiments to determine whether the housing and ultrasonic transducer have a desired vibration mode at a targeted ultrasonic communication frequency; optimizing the ultrasonic transducer or the design of the housing based on the results of the first and second finite element methods analysis and water tank experiments; verifying a resonance frequency and amplitude of the optimized ultrasonic transducer using finite element method analysis and water tank experiments; and selecting a final ultrasonic transducer and housing design based upon the results of the verifying step.
 19. The method of claim 18, wherein the conducting a second finite element analysis and water tank experiments step includes at least one of the steps of conducting water tank experiments and scanning laser vibrometer (SLV) measurements.
 20. The method of claim 18, wherein the verifying step includes at least one of the steps of conducting water tank experiments and scanning laser vibrometer (SLV) measurements. 